(89 days)
The DEKA ACE Pump System is intended for the subcutaneous delivery of insulin, at set and variable rates, for the management of diabetes mellitus in persons requiring insulin, ages six and above. The pump is able to reliably and securely communicate with compatible, digitally connected devices, including automated insulin dosing software, to receive, execute, and confirm commands from these devices. The pump is intended for single patient, home use and requires a prescription.
The bolus calculator is indicated for use for aiding the bolus insulin dosage for management of diabetes mellitus based on consumed carbohydrates, operator entered blood glucose, insulin to carbohydrate ratio, target glucose values, and current insulin on board.
The DEKA ACE Pump system is a modification of the previously cleared DEKA ACE Pump System (K213536). The modified device is a wearable alternate controller enabled (ACE) insulin infusion pump (DEKA ACE Pump System) with the addition of an embedded iAGC (DEKA Loop). The user interface is an iOS app that can be downloaded to a user's iPhone.
The updated system is still intended to subcutaneously deliver insulin, at set and variable rates, for the management of diabetes mellitus in persons requiring insulin. The pump is able to reliably and securely communicate with compatible, digitally connected devices to receive, confirm, and execute commands. The Pump is intended for single patient, ambulatory use and requires a prescription. The Pump is indicated for use with Humalog U-100 insulin.
The DEKA ACE Pump System is indicated for the management of mellitus in persons six years of age and greater.
The system as described in this submission is able to be integrated with an integrated Continuous Glucose Monitor (iCGM). This submission also details the integration process that was used to incorporate the DEKA Loop iAGC Algorithm onto the DEKA ACE Pump.
The DEKA ACE Pump System consists of the following durable and disposable components:
- Pump: A durable pump that incorporates fluid delivery algorithms and interfaces to a cassette, external wireless user interface, and iCGM. The pump is powered by a rechargeable lithium ion battery.
- Cassette: A single-use pumping cassette that combines microfluidic valves, a pump chamber, insulin reservoir, and Acoustic Volume Sensing (AVS) measurement chamber. The cassette interfaces to a pump and off-the-shelf infusion sets.
- DEKA Loop App: An iOS mobile application that serves as the primary user face for the system. The DEKA Loop app can be downloaded onto the user's personal iPhone.
The provided text is a 510(k) summary for the DEKA ACE Pump System, focusing on demonstrating substantial equivalence to a previously cleared predicate device. It addresses modifications, primarily the addition of an embedded iAGC (DEKA Loop) and a change in the user interface to an iOS app, as well as a broadened age indication (from 13+ to 6+).
However, the document does not contain the specific information required to answer your request about acceptance criteria and study proving the device meets those criteria for aspects like deep learning model performance (e.g., accuracy, sensitivity, specificity, or AUC). The request is structured as if the document describes an AI/ML-based diagnostic device where performance metrics against a ground truth dataset would be evaluated.
Instead, this document describes a medical device (insulin pump) where the "performance testing" refers to engineering and quality assurance testing against technical standards and safety requirements (e.g., electrical safety, electromagnetic compatibility, biocompatibility, delivery accuracy of insulin). The "Acceptance Criteria" implicitly refer to meeting these established engineering and regulatory standards rather than statistical performance metrics of a diagnostic algorithm against a labeled test set.
Specifically:
- There is no mention of a deep learning model's performance metrics (accuracy, sensitivity, specificity, AUC) or related test set details (sample size, data provenance, ground truth establishment, expert adjudication, MRMC studies).
- The "DEKA Loop iAGC Algorithm" is mentioned as being integrated, but there are no details on how its performance was evaluated, other than "Human Factors testing demonstrates equivalent safety and effectiveness for the indicated population" (page 7). This suggests focus on usability and safety in human interaction, not algorithmic diagnostic performance.
- The document explicitly states "No clinical data was obtained in support of this premarket submission" (page 13), reinforcing that the evaluation was primarily non-clinical and focused on substantial equivalence based on existing data and engineering tests.
Given the content of the provided document, I cannot fulfill your request for the specific details outlined for an AI/ML-based diagnostic device. The available information relates to the regulatory submission for an insulin pump, which is evaluated against different types of performance criteria.
§ 880.5730 Alternate controller enabled infusion pump.
(a)
Identification. An alternate controller enabled infusion pump (ACE pump) is a device intended for the infusion of drugs into a patient. The ACE pump may include basal and bolus drug delivery at set or variable rates. ACE pumps are designed to reliably and securely communicate with external devices, such as automated drug dosing systems, to allow drug delivery commands to be received, executed, and confirmed. ACE pumps are intended to be used both alone and in conjunction with digitally connected medical devices for the purpose of drug delivery.(b)
Classification. Class II (special controls). The special controls for this device are:(1) Design verification and validation must include the following:
(i) Evidence demonstrating that device infusion delivery accuracy conforms to defined user needs and intended uses and is validated to support safe use under actual use conditions.
(A) Design input requirements must include delivery accuracy specifications under reasonably foreseeable use conditions, including ambient temperature changes, pressure changes (
e.g., head-height, backpressure, atmospheric), and, as appropriate, different drug fluidic properties.(B) Test results must demonstrate that the device meets the design input requirements for delivery accuracy under use conditions for the programmable range of delivery rates and volumes. Testing shall be conducted with a statistically valid number of devices to account for variation between devices.
(ii) Validation testing results demonstrating the ability of the pump to detect relevant hazards associated with drug delivery and the route of administration (
e.g., occlusions, air in line, etc.) within a clinically relevant timeframe across the range of programmable drug delivery rates and volumes. Hazard detection must be appropriate for the intended use of the device and testing must validate appropriate performance under the conditions of use for the device.(iii) Validation testing results demonstrating compatibility with drugs that may be used with the pump based on its labeling. Testing must include assessment of drug stability under reasonably foreseeable use conditions that may affect drug stability (
e.g., temperature, light exposure, or other factors as needed).(iv) The device parts that directly or indirectly contact the patient must be demonstrated to be biocompatible. This shall include chemical and particulate characterization on the final, finished, fluid contacting device components demonstrating that risk of harm from device-related residues is reasonably low.
(v) Evidence verifying and validating that the device is reliable over the ACE pump use life, as specified in the design file, in terms of all device functions and in terms of pump performance.
(vi) The device must be designed and tested for electrical safety, electromagnetic compatibility, and radio frequency wireless safety and availability consistent with patient safety requirements in the intended use environment.
(vii) For any device that is capable of delivering more than one drug, the risk of cross-channeling drugs must be adequately mitigated.
(viii) For any devices intended for multiple patient use, testing must demonstrate validation of reprocessing procedures and include verification that the device meets all functional and performance requirements after reprocessing.
(2) Design verification and validation activities must include appropriate design inputs and design outputs that are essential for the proper functioning of the device that have been documented and include the following:
(i) Risk control measures shall be implemented to address device system hazards and the design decisions related to how the risk control measures impact essential performance shall be documented.
(ii) A traceability analysis demonstrating that all hazards are adequately controlled and that all controls have been validated in the final device design.
(3) The device shall include validated interface specifications for digitally connected devices. These interface specifications shall, at a minimum, provide for the following:
(i) Secure authentication (pairing) to external devices.
(ii) Secure, accurate, and reliable means of data transmission between the pump and connected devices.
(iii) Sharing of necessary state information between the pump and any digitally connected alternate controllers (
e.g., battery level, reservoir level, pump status, error conditions).(iv) Ensuring that the pump continues to operate safely when data is received in a manner outside the bounds of the parameters specified.
(v) A detailed process and procedure for sharing the pump interface specification with digitally connected devices and for validating the correct implementation of that protocol.
(4) The device must include appropriate measures to ensure that safe therapy is maintained when communications with digitally connected alternate controller devices is interrupted, lost, or re-established after an interruption (
e.g., reverting to a pre-programmed, safe drug delivery rate). Validation testing results must demonstrate that critical events that occur during a loss of communications (e.g., commands, device malfunctions, occlusions, etc.) are handled appropriately during and after the interruption.(5) The device design must ensure that a record of critical events is stored and accessible for an adequate period to allow for auditing of communications between digitally connected devices and to facilitate the sharing of pertinent information with the responsible parties for those connected devices. Critical events to be stored by the system must, at a minimum, include:
(i) A record of all drug delivery
(ii) Commands issued to the pump and pump confirmations
(iii) Device malfunctions
(iv) Alarms and alerts and associated acknowledgements
(v) Connectivity events (
e.g., establishment or loss of communications)(6) Design verification and validation must include results obtained through a human factors study that demonstrates that an intended user can safely use the device for its intended use.
(7) Device labeling must include the following:
(i) A prominent statement identifying the drugs that are compatible with the device, including the identity and concentration of those drugs as appropriate.
(ii) A description of the minimum and maximum basal rates, minimum and maximum bolus volumes, and the increment size for basal and bolus delivery, or other similarly applicable information about drug delivery parameters.
(iii) A description of the pump accuracy at minimum, intermediate, and maximum bolus delivery volumes and the method(s) used to establish bolus delivery accuracy. For each bolus volume, pump accuracy shall be described in terms of the number of bolus doses measured to be within a given range as compared to the commanded volume. An acceptable accuracy description (depending on the drug delivered and bolus volume) may be provided as follows for each bolus volume tested, as applicable: Number of bolus doses with volume that is 250 percent of the commanded amount.
(iv) A description of the pump accuracy at minimum, intermediate, and maximum basal delivery rates and the method(s) used to establish basal delivery accuracy. For each basal rate, pump accuracy shall be described in terms of the amount of drug delivered after the basal delivery was first commanded, without a warmup period, up to various time points. The information provided must include typical pump performance, as well as worst-case pump performance observed during testing in terms of both over-delivery and under-delivery. An acceptable accuracy description (depending on the drug delivered) may be provided as follows, as applicable: The total volume delivered 1 hour, 6 hours, and 12 hours after starting delivery for a typical pump tested, as well as for the pump that delivered the least and the pump that delivered the most at each time point.
(v) A description of delivery hazard alarm performance, as applicable. For occlusion alarms, performance shall be reported at minimum, intermediate, and maximum delivery rates and volumes. This description must include the specification for the longest time period that may elapse before an occlusion alarm is triggered under each delivery condition, as well as the typical results observed during performance testing of the pumps.
(vi) For wireless connection enabled devices, a description of the wireless quality of service required for proper use of the device.
(vii) For any infusion pumps intended for multiple patient reuse, instructions for safely reprocessing the device between uses.